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Study on the Corrosion and Wear Characteristics of Magnesium Alloy
AZ91D in Simulated Body Fluids
R. Vaira Vignesh
Department of Mechanical Engineering,
Amrita School of Engineering, Coimbatore,
Amrita Vishwa Vidyapeetham, Amrita University, India.
R. Padmanaban*
Department of Mechanical Engineering,
Amrita School of Engineering, Coimbatore,
Amrita Vishwa Vidyapeetham, Amrita University, India.
M. Govindaraju
Department of Mechanical Engineering,
Amrita School of Engineering, Coimbatore,
Amrita Vishwa Vidyapeetham, Amrita University, India.
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Study on the Corrosion and Wear Characteristics of Magnesium Alloy
AZ91D in Simulated Body Fluid
Abstract
Bioimplants made of metallic materials induce stress shielding effect and delayed
osteoblast activity during in-vivo experiments. Bioimplants also suffer corrosion, wear, and
combined effect of corrosion – wear during their service time. Bioimplants made of magnesium
alloys results in negligible stress shielding effect, owing to its similarity with bone’s elastic
modulus. However the soft matrix of magnesium alloy is susceptible to high wear rates. In this
study, magnesium alloy AZ91D is subjected to corrosion test (immersion and electrochemical),
adhesive wear and simultaneous corrosion – wear test to test the significance of the body fluid in
the corrosion – wear rate of the bioimplants. The surface morphology, elemental composition, and
phase composition of the specimens are characterized using FE-SEM, EDS, and XRD analytic
techniques. The results indicate that the simulated body fluid has significant effect on the corrosion
rate and corrosion – wear rate of the specimens.
Keywords: Magnesium alloy, Adhesive wear, Corrosion, Simulated Body Fluid, Radial Basis
Function
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1. Introduction
The biocompatible nature has enabled magnesium and magnesium alloys as one of the
candidature materials for bioimplants application [1, 2]. The first response of human immune
system to bioimplant is adhesion of protein to the surface of the bioimplants. This protein coating
corrodes the bioimplant material. Due to high chemical activity, bioimplants made of magnesium
alloys are prone to high corrosion rates with evolution of hydrogen gas [3, 4]. The rapid evolution
of hydrogen gas during corrosion of the bioimplant is a lethal phenomenon to the neighboring
tissues [5]. So the bioimplants should be engineered to withstand the effects of protein coating,
physiological pH, chloride ion from physiological fluid, change in human body temperature, and
have a controlled corrosion rate.
The first generation of biomedical bioimplants stressed on physical properties similar to
that of the replaced bone and minimized toxicity to the neighbor tissue [6, 7]. The second
generation of biomedical bioimplants emphasized on the ability of the biomaterials to (i) interact
with physiological environment (ii) enhance tissue bonding and osteoblast activity (iii) degrade
progressively with healing of tissues or bone. The current third generation of bioimplants is
designed to stimulate precise cellular response at the molecular level [8-13]. The material chosen
for biodegradable bioimplant should have gradual loss in mechanical strength and material by
corrosion, which should be counteracted by the newly forming bone [14, 15]. With mechanical
properties similar to that of bone, magnesium alloy AZ91D could be used for bioimplants.
However the corrosion rate of AZ91D is rapid in the chloride containing physiological
environment. The corrosion rate and hence the properties of AZ91D could be contrived using
various processing or coating techniques such as heat treatment, micro arc oxidation, vapor
deposition etc.
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Toshiyuki Nishio et al., [16] found that the microstructure of unidirectionally solidified
AZ91D alloy, consisted of α phase and nano sized β phase particles dispersion. The dispersion of
β phase increased tensile strength (TS) of processed alloy two folds. Mamoru Mabuchi et al., [17]
found that isotropic grain shape of directionally solidified AZ91D alloy enhanced the TS and proof
stress at 200 oC. Shanthi et al, [18] compared the wear behavior of recycled AZ91D alloy
(mechanical milling) and cast AZ91D alloy. The fine grained structure produced by mechanical
milling process did not increase the adhesive wear resistance, over a range of velocity at normal
load of 10N. Zafari et al., [19] found the critical temperature for transition of wear from mild to
severe in AZ91D alloy at various normal loads. Severe plastic deformation was observed at normal
load of 40 N and at testing temperature of 100oC. The formation of oxide layers at lower normal
load of 5N, increased the wear resistance at temperatures 100oC to 250oC. Severe softening of the
alloy at temperatures above 300oC, dramatically reduced the wear resistance of the alloy.
Zafari et al., [20] found that the formation of oxide layer decreased the wear rate of AZ91D
by 8% while the wear rate increased with increase in test temperature beyond 100oC. Softening of
β phase and formation of more slip systems, reduced the hardness and wear resistance. Chen and
Alpas [21] found that increase of contact temperature above 74°C, inducted severe wear in AZ91D
alloy during adhesive wear test. The wear rate and contact temperature increased with sliding
distance during dry sliding wear tests.
Witte et al., [22] found that AZ91D has good biocompatibility and corrosion resistance in
in-vivo studies. Choudhary et al., [23] found that AZ91D alloy is susceptible to stress corrosion
cracking in simulated body fluid (SBF) solution in the regime of low strain rate. They observed
transgranular cracks in the fractured specimens, though intergranular SCC and combined SCC was
prevalent in AZ91D alloy. Xue et al., [24] found that the in vivo corrosion rate of AZ91D alloy
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was lower than the in-vitro corrosion rate (SBF at 37°C). No biocompatibility issues were observed
for implanation period of two months. Walter et al., [25] investigated the effect of surface
roughness on the polarization resistance of AZ91D alloy tested in SBF and found that the alloy
with rough surface had lower polarization resistance than smooth surfaced alloy. The severity of
localized degradation of was higher for the specimen with rough surface. Tahmasebifar et al., [26]
studied the effect of pressure molding process variables on the cell adhesion and proliferation
properties of AZ91D alloy. The plates with high porosity and rough texture increased the cell
adhesion and proliferation. Wen et al., [27] studied the bio-degradability and surface chemistry of
AZ31D and AZ91D alloys subjected to immersion and electrochemical tests in modified SBF.
With increase in immersion period from 1 day to 24 days, the corrosion rate of AZ91D was
significantly lower than that of AZ31D.
The mechanical and tribological behavior of alloys depends on the corrosivity of the
environment, in which the alloys deliver their functionality. So a study to investigate the effect of
corrosive physiological environment on the wear rate of AZ91D alloy becomes obligatory. In this
study, an attempt has been made to analyze the effect of corrosive SBF environment (Dulbecco’s
phosphate buffered solution) on the wear rate of the AZ91D specimens. The effect of wear process
parameters on the adhesive wear rate and corrosion – wear rate was also investigated. A hybrid
model (polynomial function and radial basis function) was developed to investigate the effect of
adhesive wear parameters of process on the wear rate of specimens. The corrosion rate of AZ91D
was evaluated by conducting immersion test and electrochemical corrosion test. The influence of
corrosion products on the corrosion mechanism of AZ91D in SBF was also investigated.
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2. Materials and Methods
2.1 Base material
Rolled AZ91D plate of thickness 4 mm was used in the study. Chemical composition was
analyzed using optical emission spectroscopy and the composition is given in the Table 1.
Table 1. Composition of as cast AZ91D alloy
Element Al Zn Si Mn Fe Cu Ni Mg
Composition (wt. %) 8.72 0.51 0.04 0.31 0.001 0.002 0.01 Balance
2.2 Base material characterization
2.2a Microstructure
Specimens of dimension 10 mm x 10 mm were cut from the base material and mounted
using cold setting compound. The surface of the specimens were prepared as outlined by the
standard ASTM E3 – 11. The surface of the specimen was prepared using automatic disc grinder
using different grades of abrasive sheet, starting from coarse grade abrasive sheet to very-fine
grade abrasive sheet. A mirror polish was obtained in the specimen by polishing the specimen in
diamond slurry, which was followed by polishing in alumina suspension against soft velvet cloth.
That was followed by The etchant was prepared by mixing 100 ml of 95% ethanol, 6 g picric acid,
5 ml acetic acid and 10 ml distilled water, as prescribed ASTM E407 – 07. The polished surface
of the specimens was etched for 10 seconds by a gentle swab using cotton dipped in etchant, which
was in turn followed by a cold water rinse. The microstructure was observed in an optical
microscope (Make: Carl Zeiss, Model: Axiovert 25).
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2.2b Microhardness test
As described in the microstructure section, the specimens were prepared for microhardness
test (unetched). Vicker’s microhardness measurements were made using a microhardness tester
(Make: Mitutoyo, Model: MVKH1) as outlined by the standard IS 1501:2002. The diamond
indentor was plunged into the specimen under an axial load of 9.80 N and the indentor was
withdrawn after 15 s.
2.2c Tensile test
The specimens for tensile test were prepared and tested in a universal testing machine
(Make: Tinius Olsen, Model: H25KT) as per the guidelines of the standard ASTM B557 – 10. The
dimensions of the tensile test specimens are as follows: gauge length: 50.8 mm, reduced section
width: 12.7 mm, reduced section length: 57.2 mm, width of grip section: 19.0 mm, length of grip
section: 50.8 mm. The stress – strain graph was plotted by increasing the strain (incremental value
of 0.01) and obtaining the force correspondingly. The yield strength was determined by offset
method (0.2%).
2.3 Corrosion and Wear tests
2.3a Immersion corrosion test
The immersion test was performed to assess the change in pH of the SBF and corrosion
rate of the base material with increase in time. The SBF used for the immersion test was Dulbecco’s
Phosphate Buffered solution. The specimens for immersion test were prepared and tested in SBF
as per the guidelines of the standard ISO 10993 – 15. The composition of the SBF solution is given
in the Table 2. The temperature of the solution was maintained at 37±0.1°C using a temperature
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controlled water bath and the pH of the SBF solution was measured using a pH meter with a
sensitivity of ±0.01.
Table 2. Composition of Dulbecco’s phosphate buffered solution
Sl. Component name Chemical formula Concentration
(mg / L)
1 Anhydrous Calcium Chloride CaCl2 100
2 Anhydrous Magnesium Chloride MgCl2 47
3 Potassium Chloride KCl 200
4 Potassium phosphate monobasic KH2PO4 200
5 Sodium Chloride NaCl 8000
6 Anhydrous Sodium Phosphate dibasic Na2HPO4 1150
2.3b Electrochemical Corrosion test
The specimens for electrochemical corrosion test were cut from the base material to the
required dimension of 60 mm x 10 mm. The surface of the specimens were prepared as per the
procedure outlined in the section Microstructure and degreased with acetone. The prepared
specimens were placed in a desiccator filled with calcium chloride (CaCl2) to avoid the ill effects
of moisture and air. The specimens were masked using an insulation tape and an area of 1 mm2
was left unmasked for exposure to SBF solution, which is Dulbecco’s phosphate buffered solution.
The electrolyte solution was prepared by mixing the essential amount of salts in distilled water as
listed in Table 2. The specimen (working electrode), platinum wire (counter electrode), and
standard calomel electrode (reference electrode) constituted the electrochemical cell setup. The
electrochemical cell setup was immersed in a water bath, which was maintained at a physiological
temperature of 37±0.1°C and a physiological pH of 7.0.
Potentiodynamic polarization is one of the techniques in electrochemical corrosion test
used to deduce the corrosion current density, from the net current of anodic and cathodic
polarization by polarizing the test specimen in the electrolyte. Electrochemical workstation (Make:
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CH Instruments, Model: 680 Amp Booster) was used to perform potentiodynamic polarization
test. The potentiodynamic polarization test was performed in line with the standard ASTM G5-94.
Open circuit potential was established for the specimen for an immersion period of 120 minutes
and that potential was chosen as reference potential for conducting the potentiodynamic
polarization tests. The specimens were polarized at a scan rate of 5 mV.s-1 in the potential range of
-2.5 V to +2 V. The current sensitivity was chosen as 10-1 μA for the ECC tests.
2.4 Adhesive wear test
AZ91D samples of dimension 10 m x 10 mm were mounted in a steel hollow tube of outer
diameter 12 mm, inner diameter of 10 mm and height of 50mm, using cold setting compound to
prepare adhesive wear test specimens. The specimens were cleaned with acetone and weighed
using a precision weighing balance with a readability of 0.0001 g. The wear test was conducted at
par with the guidelines of the standard ASTM G99 – 95a in a pin on disc wear tester (Make: Ducom,
Model: TR20LE). The wear test parameters chosen for the study were load at the wearing contact
(load), relative sliding speed between the contacting surfaces (velocity) and accumulated sliding
distance (distance).
2.4a Statistical modelling
Face centered central composite design was used to develop the design matrix and generate
a mathematical model to interrelate the wear test parameters with the wear rate of the specimens.
The chosen level of process parameters and the design matrix for experimental trials for adhesive
wear test is given in Table IV.
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The regression models developed by response surface designs could not map the response
variables that have complex non-linearity characteristics with the input process parameters [28].
A hybrid model integrating the polynomial function and radial basis function was developed to
study the effect of wear process parameters on the adhesive wear rate of the specimens. Radial
Basis Function (RBF) is a special class of function and it is typically of Gaussian type [29]. The
advantage of multiquadratic RBF over Gaussian type is that it delivers finite global response and
it is given by the equation (1)[30].
f(𝑥) =√𝑟2 + (𝑥 − 𝑐)2
𝑟 (1)
Multiquadratic RBF was chosen to build the model for the response variable (adhesive wear rate).
The characteristic equation for function approximation using RBF network is given by equation
(3).
𝑅𝐵𝐹 = 𝑓(𝑥) = ∑ 𝑤𝑖 ∗ ∅(||𝑥 − 𝑥𝑖||)
𝑛
𝑖=1
(2)
Where 𝑓(𝑥) is the approximation function, 𝑛 is the number of RBFs, 𝑤𝑖’s are the weights. The
characteristic polynomial function– RBF mathematical model is given by equation (4).
y(𝑥) = PF + RBF (3)
Where 𝑦 is the response variable, 𝑃𝐹 is polynomial function and 𝑅𝐵𝐹 is radial basis function. If
the polynomial function is of degree 1, a linear – RBF is obtained.
2.5 Corrosion – wear test
A new approach was established to study the combined effect of corrosion and wear rate
of the specimens. The SBF is heated to 37±0.1°C using a temperature controlled water bath. The
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flow of the SBF was controlled using a control valve. The specimens were clamped in the adhesive
wear tester and the setup was confined using an enclosure. The wear test was performed in
accordance with the standard ASTM G99 – 95a with the flow of SBF (corrosive liquid). The
corrosion – wear test parameters were chosen similar to that of adhesive wear test parameters to
explicitly study the effect of SBF fluid on the corrosive wear rate of the specimens.
2.6 Metallurgical characterizations post corrosion and wear tests
The surface morphologies of the specimens subjected to tensile test, immersion test,
electrochemical corrosion test, adhesive wear test and corrosion wear test were observed using a
field emission scanning electron microscope (Make: Zeiss Sigma). The images were obtained at
electron acceleration voltage of 5kV and 10kV at various levels of magnification. The elemental
composition and the elemental map of the corroded specimens was determined using energy
dispersive x-ray spectroscopy (Make: Bruker). The constitutional phases of the base material,
adhesive wear test debris and corrosion – wear test debris were analyzed using X – ray
diffractometer (Make: Rigaku, Model: Ultima 4). XRD results of the specimens were obtained at
continuous scanning mode using Copper Kα radiation at a scan rate of 2° per minute.
3. Results and Discussion
3.1 Base material characterization
3.1a Microstructure
The optical micrograph of the base material at 200x magnification displaying well-
developed α – Mg (α phase) dendrites with secondary arms is shown in the Figure 1. Beyond the
solubility limit of Al in Mg, a brittle intermetallic secondary phase β – Mg17Al12 (β phase)
precipitated out from the supersaturated primary phase α phase of the alloy. The phases present in
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the base material are identified as α phase, β phase and (α + β) eutectic phase. Picric acid in the
etchant darkened α phase and so α phase / β phase was observed as dark region / bright region in
the micrograph respectively. The coarse branched structure observed at the grain boundaries and
inter dendritic region (gray region) was identified as eutectic phase. XRD analysis was performed
to investigate the existing phases present in the base material AZ91D. As shown in the Figure S1,
distinct diffraction peaks were observed for α phase and β phase of the alloy AZ91D. Owing to
the lesser concentration of Zn in the matrix, diffraction peaks of Mg – Zn phases were not detected.
3.1b Microhardness
Vicker’s microhardness was measured along a horizontal line in the specimen at 10
instances that were located at a distance of 1 mm from the previous instance (indentation). The
average microhardness of the base material was found to be 57.9±3.15 Hv. The standard error of
the measurements was 0.996438.
3.1c Tensile test
The stress – strain graphs of three tensile test specimens are shown in the Figure S2. The
test specimens exhibited an average yield strength (offset = 0.2%) of 135 MPa. As shown in the
Figure 2, large porosities and oxide layers were observed in the FE-SEM fractography of the
fractured surface. The fractured surface with dimples as primary feature indicated ductile fracture
[31, 32]. The β phase network at the grain boundaries tends to crack or debond from the matrix
under lower stress during tensile deformation [33]. Therefore brittle fracture was observed at some
instances on the fractured surface.
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3.2 Corrosion and Wear test
3.2a Immersion test
The concentration of the Hydrogen ions (H+) in the SBF was measured using a pH meter.
It is observed from the Figure S3 (a) that the concentration of H+ in SBF decreases with increase
in immersion period. This indicated the evolution of H2 gas as a result of corrosion phenomenon
on the surface of the specimens. The corrosion products on the surface of the specimens immersed
in SBF were cleaned using chromic acid and then the mass loss was calculated. The rate of
variation of mass decreased and became stable with increase in immersion time. The corrosion
rate of the specimens immersed in SBF for different intervals of time is shown in the Figure S3
(b). The corrosion rate of the specimen after 24 hours of immersion was 4.37 mm.year-1. The
corrosion rate steadily decreased and stabilized at an average corrosion rate of 1.05 mm.year-1 after
144 hours of immersion. The corrosion rate of the specimens decreased by a factor of 50%, 29%,
22%, 10%, 0.23% and 0.02% in the proceeding days of immersion.
The surface morphology of the specimens was observed using FE-SEM after immersion in
SBF for different time lengths. The surface of the specimens IC1, IC3, IC5 and IC7 is shown in
the Figure 3 (a), Figure 3 (b), Figure 3 (c) and Figure 3 (d) respectively. The surface was covered
by a corrosion layer, with many shallow cracks and micro pores on its surface. During initial hours
of immersion, the formation of Mg(OH)2 layer acted as barrier to prevent the matrix from
absorbing Ca and P from the SBF. Mg(OH)2 layer is vulnerable in the presence of chloride ions
(Cl-) [34]. Presence of Cl- ions in SBF and layered structure of Mg(OH)2, cracked the continuous
corrosion layer of Mg(OH)2 [15]. Flower like clusters bloomed over the surface of the specimen
after an immersion period of 24 hours, as shown in the Figure 3 (a). As observed from the Figure
3 (d), the flower like structures fell off from the surface, with increase in immersion time. The
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deposition of the corrosion products suppressed the corrosion rate of the specimens and reached a
stable state after 144 hours of immersion. The flower like corrosion products could be magnesium
carbonate, sulphate or phosphate.
Table 3. EDS analysis of the specimens corroded in immersion test
Sl. Element
Normalized concentration
Wt. % Atomic concentration Wt. %
Error (3 σ)
Wt. %
IC1 IC7 IC1 IC7 IC1 IC7
1 Aluminium 0.16 0.11 0.13 0.09 0.10 0.10
2 Magnesium 12.32 15.97 11.17 14.59 1.42 1.88
3 Sodium 1.40 1.93 1.34 1.86 0.28 0.36
4 Potassium 0.07 0.05 0.04 0.03 0.09 0.09
5 Calcium 21.98 18.74 12.08 10.38 0.12 1.22
6 Chlorine 0.46 0.60 0.29 0.38 1.35 0.13
7 Oxygen 44.61 41.41 61.43 57.48 11.55 11.22
8 Phosphorous 19.01 21.19 13.52 15.19 1.53 1.77
Total 100 100 100 100 - -
EDS analysis was performed on the corroded specimen to quantify the elements present in
the corrosion products. The result of the EDS analysis of the corroded specimens after 24 hours
(IC1) and 168 hours (IC7) of immersion are given in the Table 3. The peaks indicated the presence
of Mg, Na, Ca, P, Cl, O elements in the corrosion products. During initial period of immersion,
increase in Ca/P ratio increased the corrosion rate of the specimens. However, the Ca/P ratio
decreased with increase in immersion time, reducing the corrosion rate. The reduction in Ca on
the surface of corroded specimen favored the formation of hydroxy apatite layer
(Ca10(PO4)6(OH)2) or calcium magnesium phosphate layer (Ca10-xMgx(PO4)6(OH)2) [8-10, 13].
Previous studies proved that the formation of hydroxyapatite layer on the bioimplant material
support the bone growth and bioimplant – bone integration [22, 35]. Elemental mapping of Mg,
Al, Ca, P and O in the corroded area of specimen IC1 and IC7 are shown in the Figure 4 (a) and
Figure 4 (b) respectively. The elemental mapping revealed that the corrosion products increased
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with increase in immersion time. The high concentration of Ca and P in the corrosion layer of the
specimen IC7 is attributed to the Ca – P salt containing Mg and / or Mg(OH)2.
XRD analysis of the corroded specimen IC7 is shown in the Figure S4. Prominent peaks
were detected for α phase and β phase. Less intense peaks of MgO and Mg(OH)2 were also detected
in XRD. Besides many peaks present in the 2θ range between 20° and 35° indicated the presence
of Ca10(PO4)6(OH)2 or Ca10-xMgx(PO4)6(OH)2 on the corrosion layer.
The corrosion mechanism of the AZ91D is significantly influenced by microstructural
phases in the alloy matrix and the composition of the SBF solution. As shown in the Figure 5 (a),
many circle like patches were observed on the FE-SEM image of the specimen IC7 after removal
of corrosion products using chromic acid. At higher magnification, protruded structures with
shallow pits were observed. When the specimen IC7 was immersed in chromic acid, low
dissolution of β the phase resulted in protrusions while high dissolution of α phase resulted in
shallow pits. It was observed that the dissolution propensity of α phase, left relatively stable grain
boundaries of β phase. This attests that the β phase was homogeneously distributed in the matrix
and acts as barrier to corrosion.
3.2b Electrochemical Corrosion test
After establishing a stable open circuit potential, the specimen was potentiodynamically
polarized from -2.5 V to +2.0V at a scan rate of 5mVs-1. The Tafel plot of the tested specimen is
shown in the Figure S5. The electrochemical parameters extracted from the Tafel plot are as
follows: Corrosion current, icorr = 1.943x10-6 A; Corrosion potential, Ecorr = -1.448 V. Ecorr
determines the thermodynamic tendency towards corrosion while icorr indicated the velocity of
uniform corrosion. The corrosion current was converted to corrosion rate using the equation (4).
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Corrosion rate (𝑚𝑚 𝑦𝑒𝑎𝑟⁄ ) =𝑘 × 𝑖𝑐𝑜𝑟𝑟 × 𝐸′
𝐴 × 𝜌 (4)
Where k is a constant (3272), E’ is equivalent weight in grams/equivalent (12.1525
grams/equivalent), A is exposure area (0.01 cm2) in cm2 and ρ is density (1.74 grams.cm-3) of the
specimen in grams.cm-3. The corrosion rate calculated from the Tafel region was 4.44 mm.year-1.
The corrosion rate calculated from the mass loss of the specimen was found to be lower than the
corrosion rate calculated from the Tafel region. The surface morphology of the corrosion specimen
is shown in the Figure 5 (b). The presence of micro pores and cavities on the surface of the
corroded specimen indicated high corrosion rate of the specimen in potentiodynamic polarization
test.
During the initial immersion period of the specimen, Mg in the alloy matrix dissolves and
forms a corrosion layer of Mg(OH)2. The equations describing the reaction on the surface of the
specimen are given by equation (4) to equation (6). The corrosion layer Mg(OH)2 was stirred by
the evolution of H2 gas, which promotes further corrosion of the specimen.
Mg → 𝑀𝑔2+ + 2𝑒− (5)
2𝐻2O + 2𝑒− → 𝐻2 ↑ +2𝑂𝐻− (6)
𝑀𝑔2+ + 2𝑂𝐻− → 𝑀𝑔(𝑂𝐻)2 (7)
Mg(OH)2 is relatively more active than Mg and hence they could be regarded as the defect
sites that are ideally suited for corrosion in Cl- ion rich environments. With increase in immersion
time, anodic reaction results in more dissolution of Mg2+ ions and more consumption of phosphate
and carbonate ions from the SBF solution. This increased the Cl- ion concentration in the SBF
solution. Hence, the Cl- ions are preferentially adsorbed on the specimen surface. Owing to its
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small radius, Cl- ions penetrate the corrosion layer and converts Mg(OH)2 to MgCl2. The formation
of MgCl2 from Mg(OH)2 is summarized in the equation (8).
𝑀𝑔(𝑂𝐻)2 + 2𝐶𝑙− → 𝑀𝑔𝐶𝑙2 + 2(𝑂𝐻)− (8)
The high solubility of MgCl2 in the electrolyte creates many exposed sites on the surface,
which enables more accessibility of Mg2+ ions to phosphate ions (HPO42- or PO4
3-), and Ca2+ ions
in the SBF solution. This is turn resulted in the formation Ca10-xMgx(PO4)6(OH)2 or
Ca10(PO4)6(OH)2, in accordance with the published research [27, 36]. The formation of such
compact and insoluble phosphates retarded dissolution of Mg from the surface of the specimen.
Hence the corrosion rate of the specimens decreased with increase in immersion time, which is
evident from the immersion test results given in the section 3.2a Immersion test. This layer reduced
the permeability of Ca2+ and PO43- ions into the interface between the corrosion layer and the
matrix. Hence the corrosion layer consisted of more Ca, P and O than other elements, which is in
agreement with the result of EDS element map. As evident from literature, the difference in
corrosion potential between α phase and β phase is approximately 1 V. The α phase is more anodic
with respect to the β phase, which induces micro galvanic corrosion in the matrix.
3.3 Adhesive wear
The adhesive wear test was performed by varying the wear test parameters namely normal
load, sliding velocity, sliding distance at three levels as per face centered central composite design.
Equation (9) was used to calculate the wear rate of the specimens and the calculated wear rates are
given in the Table 4.
𝑊𝑒𝑎𝑟 𝑟𝑎𝑡𝑒 (𝑔 𝑁𝑚⁄ ) =∆𝑚
𝐹 × 𝐿 (9)
1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60 61 62 63 64 65
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The wear rate of the specimen AW1 tested at a load of 9.8 N, a sliding velocity of 1 ms-1
and a sliding distance of 600 m was found to be 0.3911 g / Nm, which was the least among the
tested specimens. The metallographic examination of the worn out surface shows loose wear debris
as seen in the Figure 6 (a). The delamination of surface oxide layer or subsurface material layer
resulted in the formation of loose wear debris.
Table 4. Design matrix and experimental results of adhesive wear test
Sl. Coded Real Wear Rate (10-6)
(g / N. m) Load Velocity Distance Load (N) Velocity (m/s) Distance (m)
AW1 -1 -1 -1 9.8 1 600 0.3911
AW2 1 -1 -1 29.4 1 600 0.4535
AW3 -1 1 -1 9.8 3 600 3.4694
AW4 1 1 -1 29.4 3 600 1.9785
AW5 -1 -1 1 9.8 1 1200 2.8316
AW6 1 -1 1 29.4 1 1200 2.0493
AW7 -1 1 1 9.8 3 1200 12.3300
AW8 1 1 1 29.4 3 1200 6.7857
AW9 0 0 0 19.6 2 900 2.3413
AW10 0 0 0 19.6 2 900 2.5680
AW11 0 0 0 19.6 2 900 2.3243
AW12 0 0 0 19.6 2 900 2.4603
AW13 -1 0 0 9.8 2 900 3.4240
AW14 1 0 0 29.4 2 900 1.1451
AW15 0 -1 0 19.6 1 900 2.7381
AW16 0 1 0 19.6 3 1000 1.6480
AW17 0 0 -1 19.6 2 600 2.3129
AW18 0 0 1 19.6 2 1200 2.2747
AW19 0 0 0 19.6 2 900 2.4943
AW20 0 0 0 19.6 2 900 2.3929
The wear rate was high (12.33 g / Nm) for the specimen AW7 tested at a load of 9.8 N, a
sliding velocity of 3 ms-1 and a sliding distance of 1200 m. The surface morphology of the worn
out specimen AW7 displayed a severe wear regime, which was characterized with massive surface
deformation and large amount of wear debris, as shown in the Figure 6 (b). During wear test, the
material layer adjacent to the contact surface had suffered an extensive plastic deformation. These
plastically deformed layers extruded out of material surface, which was subsequently removed as
1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60 61 62 63 64 65
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flat wear debris particles. Hence the worn out surface had deep grooves indicating severe wear of
the specimens. XRD analysis of the worn out debris is shown in Figure S6. The XRD peaks
confirmed the presence of α phase, β phase and MgO, which indicated that the delamination of
surface oxide layer and subsurface material layer during wear process. The broadening of the peaks
indicated the plastic deformation of the material during the adhesive wear test.
A hybrid model composting of polynomial function and radial basis function was
developed using the experimental data to investigate the influence of wear test parameters on the
wear mechanism and wear rate of the specimens. The model is given by the equation (10) and was
developed with the coded level of the wear test parameters.
Wear = 1 + 2 × Distance + 6 × Load + 9 × Velocity + 4 × Distance
× Load + 5 × Distance × Velocity + 8 × Load × Velocity
+ RBF
(10)
The RBF network was developed using a multiquadratic kernel with 0 center, a global
width of 2 and regularization parameter of 0.0001. The root mean squared error (RMSE) and
coefficient of determination (R2) are the critical statistical factors that determine the prediction
efficiency of the developed model. R2 value of the model was calculated to be 0.97 and RMSE
value of the predicted value was found to be 0.03. Closeness of R2 value to one and closeness of
RMSE value to zero indicated the high prediction efficiency of the developed model.
The load at which the wear of the specimen changes either from mild wear to severe wear
or from severe wear to mild wear is known as transition load. The effect of load on the wear rate
of the specimens at various sliding velocities for a sliding distance of 600 m is shown in the Figure
7 (a). The specimens tested exhibited a transition load of 19.6 N at all sliding velocities. The wear
phenomenon changed from severe wear to mild wear at sliding velocities of 1 ms-1 and 2 ms-1 and
1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60 61 62 63 64 65
20
changed from mild wear to severe wear at a sliding velocity of 3 ms-1. The effect of load on the
wear rate of the specimens at various sliding velocities for a sliding distance of 900 m is shown in
the Figure 7 (b). The specimens tested exhibited a transition loads of 19.6 N and 23 N at sliding
velocities of 1 ms-1 and 3ms-1 respectively. The wear phenomenon changed from severe to mild
wear at 1 ms-1 and changed from mild to severe wear at a sliding velocity of 3ms-1. The wear rate
decreased with increase in load at sliding velocity of 2 ms-1. The effect of load on the wear rate of
the specimens at various sliding velocities for a sliding distance of 1200 m is shown in the Figure
7 (c). The transition load for change in wear phenomenon from severe to mild wear for the
specimens tested was 19.6 N at sliding velocities of 2 ms-1 and 3 ms-1. However no specific change
in wear phenomenon was observed for the specimens tested at a sliding velocity of 1 ms-1.
The effect of sliding distance and sliding velocity on the wear rate of the specimens is
shown in the Figure 8 (a). At low load of 9.8 N, the wear rate increased with increase in sliding
distance. Under mild wear regime, the wear mechanism transforms from oxidational wear to
delamination wear. However, at loads greater than 19.6 N, the wear rate decreased with more
sliding distance. The increase in wear resistance of the specimens slid for more distance at higher
loads indicated the formation of work hardened matrix layer. The effect of sliding distance and
sliding velocity on the wear rate of the specimens is shown in the Figure 8 (b). It is observed that
the wear rate decreased with increase in sliding velocity. The work hardening of specimens with
more slid distance decreased their wear rate. The softness of the material matrix resulted in high
wear rate for the specimens that slid less than 900 m, at slow sliding velocities of 1ms-1 and 2 ms-
1. Figure 8 (c) shows the effect of applied load and sliding velocity on the wear rate of the
specimens. It is observed that the wear rate was high for the specimen tested at low load and high
sliding velocity and low for the specimen tested at high load and high sliding velocity.
1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60 61 62 63 64 65
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3.4 Corrosion – Wear
The corrosion – wear tests were conducted in the SBF environment, adopting wear test
parameter combinations that resulted in the most and the least adhesive wear rate. The chosen level
of wear test parameters and the corresponding corrosion – wear rate is given in the Table 5. It is
observed that the corrosion – wear of the specimens was influenced by the SBF solution. The
surface morphology of the specimen CW1 and CW2 is shown in the Figure 9 (a) and Figure 9
(b) respectively. It is observed that the surface of the specimens CW1 and CW2 was devoid of
wear tracks and the friction coefficient was lower for the specimens subjected to corrosion – wear
test than the specimens subjected to adhesive wear test.
Table 5. Experimental results of corrosion – wear test
Sl.
Coded Real Corrosion Wear
Rate (10-6)
(g / N. m)
Load
(N)
Velocity
(m/s)
Distance
(m)
Load
(N)
Velocity
(m/s)
Distance
(m)
CW1 -1 -1 -1 9.8 1 600 2.17
CW2 -1 1 1 9.8 3 1200 2.41
The interaction of SBF with the specimen produced debris and striations on the surface.
The striations were higher in the specimen CW2 than the specimen CW1. Correspondingly, the
corrosion – wear rate was higher in the specimen CW2 than the specimen CW1. However the
corrosion – wear rate of specimen CW1 was higher than the specimen AW1, which had undergone
adhesive wear. The lubricating action of the SBF solution reduced the friction coefficient between
the specimen and the counter disc as well as the heat generated at the specimen – counter disc
interface. This resulted in less corrosion – wear rate of the specimen CW2.
4. Conclusions
1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60 61 62 63 64 65
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Magnesium alloy AZ91D was characterized for microstructure, microhardness and tensile
strength. The base material was subjected to corrosion test, wear test and combined corrosion –
wear test. The conclusions of the study are as follows.
Microstructure of magnesium alloy AZ91D consists of α – Mg, β – Mg17Al12 and (α+β)
eutectic phases. The β phase is distributed as coarse continuous precipitates in the matrix.
Magnesium alloy AZ91D favors formation of hydroxy apatite layer on its surface with
increase in immersion time in body fluids. The corrosion potential and the corrosion rate
interpolated from the Tafel region is -1.448 V and 4.44 mm.year-1 respectively.
Statistical modelling of the adhesive wear test elucidates the transition load with respect to
change in wear test parameters. SBF has significant influence on the wear test of the
specimens, as observed from the corrosion – wear test.
Acknowledgement
The authors are grateful to Amrita Vishwa Vidyapeetham, India for their financial support
to carry out this investigation through an internally funded research project no. AMRITA/IFRP-
20/2016-2017.
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List of Figures
Figure 1. Microstructure of AZ91D depicting the α phase (dark region), β phase (bright region)
and (α+β) eutectic phase (grey region)
Figure S1. XRD analysis of AZ91D showing the prominent peaks for α phase and β phase in the
base material AZ91D
Figure S2. Stress – Strain graph of AZ91D
Figure 2. Fractography of the tensile test specimen at magnification of 4000 X showing dimples
and ruptured surface indicating a combined ductile and brittle fracture mechanism
Figure S3. a) Increase in pH value of SBF indicates the evolution of H2 gas with increase in
immersionn time; b) Decrease in corrosion rate of AZ91D indicates the formation of corrosion
resistant layer on the surface with increase in immersion time
Figure 3. Surface morphology of the specimen a) IC1 after 24 hours of immersion showing flower
like clusters; b) IC3 after 72 hours of immersion with diminished flower like clusters; c) IC5 after
120 hours of immersion showing wide cracks and a few flower like clusters; d) IC7 after 168 hours
of immersion showing a few flower like clusters and a thin layer of corrosion products on the
surface
Figure 4. Elemental mapping of the specimen a) IC1 after 24 hours of immersion; b) IC1 after 168
hours of immersion indicating the high deposition of Ca and P on the surface
Figure S4. XRD analysis of the corrosion products of specimen IC7 after 168 hours of immersion
showing the prominent peaks for α phase, β phase, MgO and Hydroxyapatite
1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60 61 62 63 64 65
25
Figure 5. a) Surface of the specimen IC7 after cleaning the corrosion products showing protrusion
(β phase) and shallow pits (α phase, which was dissolved by chromic acid); b)Surface morphology
of AZ91D after potentiodynamic polarization test showing micropores at magnification of 3000X
Figure S5. Potentiodynamic polarization plot of AZ91D in SBF solution at 37±0.1°C
Figure 6. FE-SEM image of the specimen after adhesive wear test a) Specimen AW1 exhibiting
mild wear; b) Specimen AW7 exhibiting severe wear
Figure S6. XRD analysis of specimen AW7 indicatign the presence of oxide layer along with the
microcontiuents of the alloy AZ91D
Figure 7. Effect of axial load and sliding velocity on the adhesive wear rate of specimens showing
transition load at a sliding distance of a) 600 m; b) 900 m; c) 1200 m
Figure 8. Effect of wear test parameters a) Distance and Velocity; b) Distance and Load; c) Load
and Velocity on the wear rate of AZ91D
Figure 9. FE-SEM image of the specimen a) CW1; b) CW2 after corrosion – wear test
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